Diagnostic imaging apparatus with airflow cooling system

ABSTRACT

A diagnostic imaging system, which can be a mobile or stationary surgical CT imaging system or an MRI system, comprises an internal airflow cooling system that includes an air intake opening and an air outtake opening that are positioned near the ground and direct air flow away from the sterile surgical field.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims the benefit of U.S. Provisional Application No.61/315,462, filed Mar. 19, 2010, the entire contents of which areincorporated herein by reference.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

N/A

BACKGROUND OF THE INVENTION

The present invention relates to a cooling system for a diagnosticimaging apparatus.

A conventional computed tomography (CT) x-ray scanner is a relativelylarge, stationary device having a fixed bore, and is typically locatedin a dedicated x-ray room, such as in the radiology department of ahospital. A number of components of the x-ray scanning device, such asthe x-ray source and high-voltage generator, are known to generate alarge amount of heat during operation of the system. Other components,such as the x-ray detector, are very sensitive to heat. Conventional CTscanners typically include cooling systems to manage heat flow, andensure that the heat generated by the system does not interfere with theoperation of the imaging apparatus. These cooling systems can berelatively large and complex, which is not a problem with conventionalsystems, which are very large and fixed in place.

It would be desirable to have true X-ray CT functionality in a mobiledevice that can, for example, easily be moved to different areas of ahospital and can be used at the point of care, such as in an operatingroom or emergency room. However, making an x-ray CT scanner mobile,while maintaining the same level of functionality as conventional fixedsystems, requires substantial changes to overall system architecture.Ideally, a mobile system should be made smaller, more compact andlightweight relative to conventional systems. Moreover, otherconsiderations need to be taken into account where the system isintended to be used in a sterile environment. The conventionaltechniques for cooling are not well adapted to small and/or mobileimaging devices.

BRIEF SUMMARY OF THE INVENTION

According to one aspect of the invention, a diagnostic imaging systemcomprises an internal airflow cooling system that includes an air intakeopening and an air exhaust opening that are positioned near the groundand direct air flow away from a sterile surgical field. According tosome embodiments, the diagnostic imaging system is a mobile orstationary surgical CT imaging system or a magnetic resonance (MR)imaging system.

In certain embodiments, the imaging system includes an air duct system.The imaging system also includes a gantry that is a generally O-shapedhousing that contains a plurality of imaging components. The interiorhousing of the gantry can be in fluid communication with the air ductsystem at two locations that, in one embodiment, are generally opposedto one another on the gantry. The gantry includes a generally enclosedor sealed interior housing.

In one embodiment, the imaging system further includes a generallyC-shaped support gimbal, and the air duct system is at least partiallycontained within the gimbal. The gimbal supports the gantry, andattaches to the gantry at two opposed ends of the gantry to providefluid communication between the air duct system and the interior housingof the gantry. In one embodiment, the gimbal is connected to the gantryby a bearing system that includes a through-hole for providing fluidcommunication between the air duct system and the interior housing ofthe gantry. The bearing system enables the gantry to tilt with respectto the gimbal upon which it is supported.

In one embodiment, the airflow cooling system includes an air intakeopening so that air is allowed to enter the generally C-shaped gimbalclose to the ground, and an air exhaust opening wherein the air isallowed to exit the opposite side of generally C-shaped gimbal alsoclose to the ground. The air intake opening is in fluid communicationwith the interior of the gantry and, in one embodiment, air enters thegantry through a first bearing that attaches the gantry to the gimbal.The airflow passes through the gantry and, in one embodiment, exits thegantry via a second bearing located opposite the first bearing on thegantry, thus allowing the airflow to be directed through the gimbal tothe air exhaust opening.

In one embodiment, the gantry includes an airflow bifurcation systemthat forces airflow entering from a first side of the gantry to bedistributed in two directions around the interior of the gantry and toexit through an opening on the opposite side of the gantry. Thebifurcation system can include a plurality of bulkheads along the topand bottom paths of the gantry that direct the air along the top and thebottom of the gantry and prevent airflow in the opposing direction. Inone embodiment, a plurality of fans are cooperatively associated withthe bulkheads to facilitate the airflow in the desired direction.

In one embodiment, a plurality of imaging components are housed withinthe gantry, and are mounted on a rotor that rotates within the gantry.The rotor rotates around the interior the gantry during imagingprocedures (scans), and can rotate to a pre-determined angular position(or “park” position) within the gantry between imaging procedures. Thesystem can be configured such that, when the rotor is in a “park”position, in general, heat sensitive components are provided on the airintake side of the gantry and the less heat sensitive components placedon the air exhaust side of the gantry. In some embodiments, at leastsome imaging components can be provided on or within the gimbal, withthe more heat sensitive components being provided on the air intake sideof the gimbal, and the less heat sensitive components being provided onthe air exhaust side of the gimbal.

According to another aspect, the heat generating components housedwithin the gantry are generally provided proximate to the air exhaustopening when the rotor is in a park position.

In other embodiments, a method of imaging uses a diagnostic imagingsystem having an internal airflow cooling system.

In one embodiment, components within the generally O-shaped gantry arearranged so that the components less susceptible to heating effect aregenerally placed proximate to one another on a first side of the gantryand the components more susceptible to heating effects are generallyplaced proximate to one another on a second side of the gantry, oppositethe first side.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

Other features and advantages of the present invention will be apparentfrom the following detailed description of the invention, taken inconjunction with the accompanying drawings of which:

FIG. 1 is a perspective view of an X-ray CT imaging system in accordancewith one embodiment of the invention;

FIG. 2 is a cross-sectional side view of an imaging gantry and gimbalsupport with an airflow cooling system;

FIG. 3 is a cross-sectional perspective view of the gantry and gimbal ofFIG. 2;

FIG. 4 is a cross-sectional schematic illustration of the arrangement ofcomponents in the gantry according to one embodiment;

FIG. 5 is a cross-sectional perspective view of a stand-alone gantrywith an airflow cooling system according to one embodiment of theinvention; and

FIG. 6 illustrates a gantry that is tilted and rotated to illustrate anaccess panel.

DETAILED DESCRIPTION OF THE INVENTION

This application claims the benefit of U.S. Provisional Application No.61/315,462, filed Mar. 19, 2010, and is related to U.S. application Ser.No. 12/576,681, filed Oct. 9, 2009, and to U.S. Provisional ApplicationNo. 61/313,299, filed Mar. 12, 2010. The entire disclosures of theabove-referenced applications are incorporated herein by reference.

Referring to FIG. 1, a mobile imaging system 100 according to oneembodiment of the invention includes a mobile base 20, a gimbal 30, agantry 40, and a pedestal 50. The system 100 includes image collectioncomponents, such as a rotatable x-ray source and detector array orstationary magnetic resonance imaging components, that are housed withinthe gantry 40. The system 100 is configured to collect imaging data,such as, for example x-ray computed tomography (CT) or magneticresonance imaging (MRI) data, from an object located within the bore ofthe gantry 40, in any manner known in the medical imaging field. Thepedestal 50 is adapted to support a tabletop support 60 that can beattached to the pedestal 50 in a cantilevered manner and extend out intothe bore of the gantry 40 to support a patient or other object beingimaged.

The gimbal 30 is a generally C-shaped support that is mounted to the topsurface of base 20 and includes a pair of arms 31, 33 extending up frombase. The arms 31, 33 are connected to opposite sides of gantry 40 sothat the gantry ring is suspended above base 20 and gimbal 30.

In certain embodiments, the gimbal 30 and gantry 40 translate withrespect to the base 20 to provide an imaging scan. The gimbal 30includes bearing surfaces that travel on rails 25, as shown in FIG. 1,to provide the translation motion of the gimbal 30 and gantry 20. In oneembodiment, a scan drive mechanism drives the translation of the gantryand gimbal relative to the base, and a main drive mechanism drives theentire system in a transport mode. In the embodiment of FIG. 1, both ofthese functions are combined in a drive system 70 that is locatedbeneath the gimbal 30.

In one embodiment, the gimbal 30 and gantry 40 rotate about an axisrelative to the base. FIG. 6 illustrates the gimbal 30 and gantry 40partially rotated. According to another aspect, the gantry 40 can tiltrelative to the gimbal 30, as is shown in FIG. 6.

In certain embodiments, the base of the system is omitted, and thegimbal 30 sits directly on the ground to support the gantry 40. In otherembodiments, such as shown in FIG. 5, the gimbal is omitted, and thegantry 40 is a stand-alone gantry that sits on the ground.

FIG. 2 is a cross-sectional view of the gimbal 30 and gantry 40according to one embodiment of the invention. The gantry 40 in thisembodiment is a generally O-shaped housing that contains a rotor 41 inthe interior of the housing. The rotor 41 rotates within the interior ofthe gantry, as is known, for example, in conventional X-ray CT scanners.A plurality of imaging components, such as an x-ray source and x-raydetector, are mounted to the rotor 41, and thus rotate around theinterior of the gantry 40 in coordination with the rotation of the rotor41. A suitable drive mechanism can drive the rotation of the rotor 41around the interior of the gantry 40, as is known in the art. The drivemechanism can be controlled by a system controller that controls therotation and precise angular position of the rotor 41 with respect tothe gantry 40, preferably using position feedback data, such as from aposition encoder device.

The imaging system further includes an airflow cooling system, as shownin FIG. 2. The airflow cooling system in this embodiment includes an airintake opening 34 and an air exhaust opening 35. Both openings 34, 35can be located at or near the bottom of the gimbal 30. In oneembodiment, the air intake opening 34 and/or the air exhaust opening 35are located below the patient or object being imaged, generally belowthe gantry bore, or the gantry housing, and preferably below the area ofa surgical sterile field. In the embodiment of FIG. 2, the air exhaustopening 35 is on the opposite side of the gimbal 30 from the air intakeopening 34, which helps prevent the generally hotter exhaust air fromentering the intake opening 34 and recirculating through the coolingsystem.

According to one aspect, ambient air is drawn through the air intakeopening 34 and up through a duct 36 that extends through the interiorone of the arms 31 of the gimbal 30. One or more fans or blowers (notshown) can be provided proximate the intake opening 34 or within theduct 36 to facilitate the flow of air. At the top of the arm 31, theduct 36 is in fluid communication with the interior housing of thegantry 40. The gimbal 30 can be connected to the gantry 40 by a bearingsystem 39 that enables the “tilt” motion of the gantry (FIG. 6). Thebearing system 39 can include a through-hole for providing fluidcommunication between the air duct 36 and the interior of the gantry 40.This is shown more clearly in FIG. 3.

As the air enters the interior of the gantry 40, the flow of air isbifurcated, as indicated by the arrows, so that a portion of the airflow is distributed to the top side of the gantry and a portion of theair is distributed to the bottom side of the gantry. The two air flowsrejoin each other on the opposite side of the gantry 40, where the airthen exits the gantry 40 into a duct 37, which extends along theinterior of gimbal arm 33. The air then exits the system through exhaustopening 35. One or more fans or blowers (not shown) can be providedproximate the exhaust opening 35 or within the duct 37 to facilitate theflow of air in the direction indicated by the illustrated arrows.

Within the gantry 40, a plurality of bulkheads 43 are provided in oneembodiment to help direct the airflow in the desired pattern. Thebulkheads 43 are mounted to the rotor 41, and generally divide theinterior of the gantry 40 into a plurality of volume segments. Eachbulkhead 43 can include one or more openings to permit air to flowthrough the bulkhead 43. A fan or blower (not shown) can be provided inthe openings of the bulkheads 43 to direct the air to flow in thedesired direction, and to prevent backflow of air in the oppositedirection. One or more fans or blowers can be provided elsewhere in thegantry 40 to direct the flow of air in the desired pattern. Generally,at least two bulkheads 43 are provided on opposing sides of the gantryto provide the bifurcated air flow. Four or more bulkheads 43 may beprovided, as is shown in FIGS. 2 and 3. The bulkheads 43 can comprisediscrete components mounted to the rotor, such as the flat plates shownmost clearly in FIG. 3. In some embodiments, the bulkheads 43 can beintegrated with, and form part of, another component of the imagingsystem. For example, a bulkhead 43 similar to those shown in FIGS. 2 and3 can also function as a part of the housing of an imaging component,such as a high-voltage generator or an on-board processing module(computer) for an x-ray CT scanner.

The imaging system generally operates in a conventional manner to obtainimages of an object located in the bore of the gantry. For example, inthe case of an x-ray CT scan, the rotor 41 rotates within the housing ofthe gantry 40 while the imaging components, including the x-ray sourceand x-ray detector, obtain image data at a variety of scan angles.Generally, the system obtains image data over relatively shortintervals, with a typical scan lasting less than a minute, or sometimesjust a few seconds.

During these short intervals, however, a number of components, such asthe x-ray source tube and the high-voltage generator, generate a massiveamount of heat, which quickly diffuses through the gantry to heat upother components while the system is not in use. Accordingly, theairflow cooling system 80 of the invention is configured to manage andcontrol the transfer of heat in the imaging system so as to avoidoverheating and damage to the device, and further to minimize oreliminate the transfer of heat to heat-sensitive components on thegantry. In one aspect, the airflow cooling system 80 functions as a heatexchanger, taking in ambient air and circulating the air inside theinterior of the gantry, where the air absorbs heat from the imagingcomponents, and removing this heat from the system through the exhaustoutlet.

The imaging system can be configured so that when the system is notobtaining image data, the rotor 41 rotates to the same “park” positionwithin the gantry 40. During the intervals between scans, when the rotoris in the “park” position, a first group of imaging components arealways located proximate the air intake side of the gantry 40, and asecond group of imaging components are always located proximate the airoutlet side of the gantry 40. As shown in FIG. 2, for example, the firstgroup of imaging components can include the most heat sensitivecomponents, and the second group can include the components that tend togenerate the most heat.

FIG. 4 schematically illustrates an arrangement of components on therotor 41 of an x-ray CT scanner according to one embodiment of theinvention. In this embodiment, the imaging components include an x-raysource tube 42 and an x-ray detector array 45. These components aregenerally located opposite each other on the rotor 41. Other componentsinclude a high-voltage generator 44 that provides the high-voltagerequired to energize the x-ray tube 42, and a cooler system 45 thatcirculates a cooling fluid to the x-ray tube 42 to prevent the tube fromoverheating. These components are typically found in conventional x-rayCT scanning systems.

Other components on the rotor 41, however, are unique to the presentsystem, and include a computer 45, a battery-based power supply 47, anda drive mechanism 48. The computer 45 is provided on-board the rotor 41to provide at least some processing of the detected x-ray image data.The computer 45 can also provide system control functions. An advantageof providing the computer 45 on the rotor 41 is that it minimizes thedata transfer requirements between the components located on the rotor41 and processing and display devices located off the rotor 41. Thepower supply 47 can provide all the required power to the components onthe rotor 41, and generally comprises a plurality of battery packsconnected in series. The battery packs are preferably rechargeable, andare recharged during the “down-time” between image scans. A charger isprovided on the gimbal 30, for example, and interfaces with the rotor 41when the rotor is in the “park” position to recharge the battery packs.An advantage of the battery-based power supply 47 is that theconventional schemes for delivering power to the imaging components,such as complicated and expensive slip-ring systems and bulky cablesystems, can be avoided. Similarly, placing the drive mechanism 48 onthe rotor 41 helps cut down on the size and complexity of the imagingsystem, which is advantageous in terms of increasing the mobility of thesystem.

The various components on the rotor 41 can be considered in terms ofboth their sensitivity to heat, and the amount of heat they generate. Interms of sensitivity to heat, the most heat-sensitive component is thedetector 45, the performance of which is known to be highlytemperature-dependent. The battery-based power source 47 is also heatsensitive, as excessive heat can cause the battery packs to ageprematurely. The computer 46 is both heat-sensitive and also generatessome heat. The remaining components (x-ray tube 42, cooler 45, generator44 and drive mechanism 48) are not particularly heat-sensitive. However,of these, the x-ray tube 42, cooler 45 and high voltage generator 44 areby far the biggest heat generators on the rotor 41. The drive mechanism48 generates modest heat.

Accordingly, one suitable arrangement of the components on the rotor 41is illustrated in FIG. 4. The rotor 41 is depicted in the “park”position, so that the cooling system can provide maximum coolingefficiency. As can be seen in FIG. 4, the detector array 45, which ishighly heat-sensitive, is placed in close proximity to the air intakeduct 36. In one embodiment, the detector array 45 is the closestcomponent to the intake duct 36 so that the detector 45 receivesgenerally the coolest air flow. The battery-based power supply 47 andthe computer 45 are also provided on the air intake side of the rotor41, downstream of the detector 45 and upstream of the components thatgenerate the most heat. The largest heat generating components,including the x-ray tube 42 and associated cooler 45, and thehigh-voltage generator 44, are located on the air exhaust side of therotor 41, in close proximity to the exhaust-side duct 37. In oneembodiment, the x-ray tube 42 is located directly adjacent the entranceto exhaust duct 37, and is the component that is furthest downstream inthe direction of the airflow within the gantry. In other embodiments,the x-ray tube cooler 45 can be located furthest downstream and adjacentthe exhaust duct 37, as the cooler generally outputs a significantamount of heat from the tube 42. The bulkheads 43 can be provided insuitable locations on the rotor 41 to help isolate the moreheat-sensitive components from the heat-generating components, and tominimize the backflow of heated air to the heat-sensitive components.

The location of the drive mechanism 48 is not critical, since it isneither particularly heat-generating nor particularly heat-sensitive.However, there may be some benefit to placing it away from the x-raytube 42 to minimize EM interference with the tube which can affect theposition of the x-ray focal spot. In this embodiment, the drivemechanism 48 is provided beneath the detector array 45, and 180 degreesaway from the x-ray tube 42.

In certain embodiments, some components of the imaging system can belocated on the gimbal 30. For example, some electronic control andprocessing circuitry, such as the battery charger, can be provided onthe gimbal 30. As some of these electronic circuitry components can besensitive to heat, they can be provided on the arm 31 of the gimbal 30containing the air intake duct 26, and can be located within the intakeduct 26, or in thermal communication with the intake duct 26.

As previously discussed, in certain embodiments the imaging system canbe a mobile system that can be easily moved to different areas of ahospital and can be used at the point of care, such as in an operatingroom or emergency room. In many of these environments, the system willneed to meet strict requirements for sterility. These requirements wouldnot normally be applicable for the large, fixed devices currently foundin a radiology department. One advantage of the present invention isthat the airflow cooling system can provide effective cooling of theimaging components without interfering with the surgical sterile field.In general, when the imaging system is utilized in a surgical context,any part of the device that is exposed to the patient is considered tobe within the “sterile field,” and thus must be kept sterilized, drapedor otherwise isolated to prevent contamination of the patient. Thisgenerally includes all exposed parts of the system that are located atthe height of the patient table and above. In the present invention, theairflow cooling system is not exposed to the sterile field, since theonly exposed parts of the cooling system are the air inlet opening 34and air exhaust opening 35, which are located far below the patienttable 60, preferably close to the ground, and generally direct theairflow away from the sterile field. It would not be acceptable to ventthe airflow into the sterile field, since the air flows through theunsterilized interior of the gantry and could potentially carry germs orother contaminants into the sterile surgical field.

FIG. 5 illustrates an alternative embodiment of a stand-alone gantry 40with an airflow cooling system. In this embodiment, the gantry 40 has abase portion 49 that can sit on the floor or other surface, and supportsthe generally O-shaped housing in which the rotor 41 and imagingcomponents rotate. The air inlet opening 34, air exhaust opening 35 andducts 36, 37 are provided in the gantry 40 itself, as opposed to in aseparate gimbal structure. In other respects, the cooling system of thisembodiment can function substantially as described in connection withFIGS. 1-4.

FIG. 6 illustrates another aspect of the present imaging system. In thisembodiment, the gantry 40 is supported on a gimbal 30, and can tilt withrespect to the gimbal. Here, the bottom of the gantry 40 is shown tiltedupwards almost 90 degrees with respect to the gimbal. The bottom of thegantry 40 includes an opening 51 to permit easy access to the variousimaging components housed within the gantry 40. Preferably, the opening51 is sized to permit the imaging components to be removed from, orplaced into, the interior of the gantry 40, as may be required forservice, repair or periodic upgrades. In this embodiment, the opening 51is sized to permit the detector array to pass through the opening, asthe detector array is typically the largest component within the gantry.The internal gantry rotor can rotate within the gantry to allow anycomponent to be accessed through the opening 51. An access panel (notshown) can be attached over the opening 51 to seal the gantry 40 duringuse. Certain components of the imaging system, including the detectorarray, for example, will generally be too large to be inserted orremoved via the interior diameter of the gantry (i.e., through thegantry bore). The opening 51 can advantageously permit easy access toall of the components of the gantry. Although the opening 51 in thisembodiment is illustrated as a single opening on the bottom side of thegantry, it will be understood that one or more access openings can beprovided on any surface of the gantry, including at the top of thegantry.

While the invention has been described in connection with specificmethods and apparatus, those skilled in the art will recognize otherequivalents to the specific embodiments herein. It is to be understoodthat the description is by way of example and not as a limitation to thescope of the invention and these equivalents are intended to beencompassed by the claims set forth below.

1. A diagnostic imaging system, comprising: a gantry having a housingdefining an interior that contains imaging components; an airflowcooling system that directs a flow of air through the interior of thehousing of the gantry and includes an air intake opening and an airexhaust opening that are positioned near the ground.
 2. The diagnosticimaging system of claim 1, wherein the air intake opening and airexhaust opening direct air flow away from a sterile surgical field. 3.The imaging system of claim 1, wherein the system comprises a mobilesystem.
 4. The imaging system of claim 1, wherein the system comprisesand x-ray CT imaging system.
 5. The imaging system of claim 1, whereinthe system comprises a magnetic resonance imaging system.
 6. The imagingsystem of claim 1, wherein the gantry comprises a generally O-shapedhousing that contains the imaging components.
 7. The imaging system ofclaim 1, further comprising an air duct system that provides a fluidconnection between the air intake opening and the interior of the gantryat a first side of the gantry, and provides fluid connection between theair exhaust opening and the interior of the gantry at a second side ofthe gantry, opposite the first side.
 8. The imaging system of claim 7,wherein the gantry is supported by a gimbal, and the duct system isprovided in the gimbal.
 9. The imaging system of claim 7, wherein theduct system is provided in the gantry.
 10. The imaging system of claim8, further comprising a bearing system with a through-hole that connectsthe gimbal to the gantry on the two opposing sides of the gantry andallows the gantry to tilt relative to the gimbal.
 11. The imaging systemof claim 10, wherein the airflow directed from the intake opening on thegimbal is directed to enter through the bearing attached to the gantryto enter the gantry at an intake side and wherein the airflow passesthrough the generally O-shaped gantry and exits through the bearingattached to the gantry opposite the first bearing thereby allowing theairflow to be directed through an exhaust opening on the gimbal.
 12. Theimaging system of claim 1, further comprising an airflow bifurcationsystem located within gantry that forces airflow entering a first sideof the gantry to be distributed in two directions around the interior ofthe gantry and exit through a second side of the gantry, opposite thefirst side.
 13. The imaging system of claim 12, wherein the bifurcationsystem comprises a plurality of bulkheads that direct the air along thetwo directions of the gantry and prevent airflow in the opposingdirection.
 14. The imaging system of claim 13, wherein at least one fanis provided within the gantry to direct the airflow.
 15. The imagingsystem of claim 14, wherein the at least one fan is cooperativelyassociated with the bulkheads.
 16. The imaging system of claim 1,further comprising a rotor that rotates around the interior of thegantry, the imaging components being mounted to the rotor.
 17. Theimaging system of claim 16, further comprising a plurality of bulkheadsmounted to the rotor.
 18. The imaging system of claim 1, wherein heatsensitive imaging components are placed generally adjacent to another onthe gantry such that when the imaging system is not in use, the heatsensitive components are located proximate an air intake side of thegantry and less heat sensitive components are located proximate an airexhaust side of the gantry.
 19. The imaging system of claim 8, whereinat least some imaging components are provided on the gimbal, and theheat sensitive components are generally placed proximate the air intakeopening and the less heat sensitive components are generally placedproximate the air exhaust opening.
 20. The imaging system of claim 18,wherein heat generating imaging components are generally placed asclosed to the air exhaust as possible.
 21. The imaging system of claim18, wherein the gantry is enclosed or sealed.
 22. The imaging system ofclaim 1, wherein the gantry has one or more openings on an outerdiameter of the gantry for installation, removal and servicing ofcomponents within the gantry.
 23. The imaging system of claim 1, whereinthe air intake opening and an air exhaust opening are positioned belowan imaging region defined by the gantry.
 24. The imaging system of claim18, wherein the heat sensitive components include a detector array. 25.The imaging system of claim 18, wherein the heat sensitive componentsinclude at least one of a battery power source and a computer.
 26. Theimaging system of claim 20, wherein the heat generating componentsinclude at least one of an x-ray source, a high-voltage generator, andan x-ray tube cooler.
 27. A method for diagnostic imaging using animaging system, comprising: positioning an object within an imaging boreof a gantry of the imaging system; obtaining images of the object usingimaging components contained within an interior housing of the gantry;and directing a flow of air through the imaging system to cool theimaging components, the air entering and exiting the imaging system atone or more positions near to the ground.
 28. The method of claim 27,wherein the air enters and exits the imaging system at positions belowthe imaging bore of the gantry.
 29. The method of claim 27, furthercomprising: directing the flow of air away from a surgical sterilefield.
 30. The method of claim 27, further comprising: directing theflow of air through the interior housing of the gantry.
 31. The methodof claim 27, further comprising: rotating a rotor within the gantryhousing to a stationary park position when the imaging system is notobtaining images, the imaging components being mounted to the rotor. 32.The method of claim 31, further comprising: rotating the rotor to astationary park position in which heat sensitive imaging components arepositioned on an upstream side of the flow of air and heat generatingimaging components are positioned on a downstream side of the flow ofair.
 33. The method of claim 27, further comprising: directing the flowof air through a duct system in fluid communication with the interiorhousing of the gantry.
 34. The method of claim 33, wherein the ductsystem is contained in a gimbal structure that supports the gantry. 35.The method of claim 30, further comprising: directing the flow of air intwo directions around the interior of an 0-shaped gantry.
 36. The methodof claim 27, wherein the object comprises a human or animal subject. 37.The method of claim 27, wherein the images are x-ray CT scan images. 38.The method of claim 27, wherein the images are magnetic resonanceimages.